|Publication number||WO2012141975 A1|
|Publication date||18 Oct 2012|
|Filing date||5 Apr 2012|
|Priority date||12 Apr 2011|
|Also published as||US9028496, US20130090655|
|Publication number||PCT/2012/32409, PCT/US/12/032409, PCT/US/12/32409, PCT/US/2012/032409, PCT/US/2012/32409, PCT/US12/032409, PCT/US12/32409, PCT/US12032409, PCT/US1232409, PCT/US2012/032409, PCT/US2012/32409, PCT/US2012032409, PCT/US201232409, WO 2012/141975 A1, WO 2012141975 A1, WO 2012141975A1, WO-A1-2012141975, WO2012/141975A1, WO2012141975 A1, WO2012141975A1|
|Inventors||William L. TONTZ|
|Applicant||Tontz William L|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (7), Classifications (4), Legal Events (3)|
|External Links: Patentscope, Espacenet|
DEVICE FOR ESTABLISHING SUPPORTIVE FORCES IN THE BONY STRUCTURE OF A SKELETON
This application claims the benefit of U.S. Provisional Patent Application Serial No. 61/474,721, filed April 12, 2011. FIELD OF THE INVENTION
The present invention pertains generally to devices that provide support for a bone of a human skeleton. More specifically, the present invention pertains to devices that provide internal support to unhealthy bones in a human skeleton. The present invention is particularly, but not exclusively, useful as a customizable, implantable device for replicating biomechanical forces normally present inside a healthy bone of a human skeleton.
BACKGROUND OF THE INVENTION
The bones of the human skeleton serve many important structural and mechanical purposes. Among them, the bones protect organs, provide a frame to support the body, and function along with muscle and tissue to allow parts of the body to move. During these and other tasks, the bones are subjected to various forces. In particular, the bones that serve as joints in the human body, like the knee or shoulder, are subjected to increased forces during movement of various body parts. To counteract these forces, bones use biomechanical forces to remain functional. In a healthy bone, these biomechanical forces help protect the healthy bone by counteracting forces that may be randomly applied on the bone. Through the use of a radiological device, an illustration of stress lines can be developed to show the types of forces a healthy bone needs to counteract. These forces will vary based on the unique characteristics of each bone in the human skeleton. Numerous reasons can cause a bone in the human body to be weakened and require support. Support for a weakened bone can be provided either externally (i.e. outside the body), or internally, (i.e. in direct contact with a bone). In the case of external support, a splint or a cast can be placed on the skin over the weakened bone, such as a fractured femur, to provide short-term support. Regarding the case of internal support, various screws, rods, and pins can be affixed directly to the bone and are suitable for long-term support. In any of these cases, the support is directed towards allowing the bone to heal. And, in many cases, the internal or external support limits the movement or motion of the body part being supported. Furthermore, the internal or external support does not accurately replicate the biomechanical forces present in a healthy bone.
In light of the above, it is an object of the present invention to provide a device that can be implanted into a bone to replicate the biomechanical forces that are normally present in a healthy bone. Another object of the present invention is to provide a device that can be customized for a particular bone to replicate the unique biomechanical forces that are typically imposed on the bone in the human skeleton. Yet another object of the present invention is to provide a device that can be used for establishing supportive forces in the bony structure of a skeleton that is easy to use, is relatively simple to manufacture, and is comparatively cost effective.
SUMMARY OF THE INVENTION
In accordance with the present invention, a device is provided that can be implanted inside an unhealthy bone of a skeleton to provide internal support for the bone. To accomplish this, various configurations of a wire assembly can be constructed. In detail, depending on the anatomy of a particular bone, a single wire assembly, a secondary wire assembly, a bipartite wire assembly, or a compound wire assembly may be chosen for insertion into the bone. The particular assembly which is chosen is dependent on the anatomy of the bone in which the assembly is implanted and the biomechanical forces which need to be replicated to provide support to the selected bone.
Structurally, a single wire assembly in accordance with the present invention includes a base member that defines an axis. A compression plate that is centered on the axis, and is positioned at a distance "d" from the base member, is included as part of the assembly. Interconnecting the compression plate with the base member is a plurality of titanium wires. In detail, each wire in the plurality is individually coplanar with the axis, and each wire is distanced laterally from the axis, with each wire being the same lateral distance away from the axis. A central shaft is aligned along the axis and it interconnects the compression plate with the base member.
Also included in a single wire assembly is an actuator. Functionally, this actuator is used for acting on the central shaft to change the distance "d" between the compression plate and the base member. This change in the distance "d" is made through an increment "Ad", and it results in the movement of the plurality of wires between a first configuration and a second configuration. Specifically, in the first configuration, the wires are substantially parallel to each other. Thus, in this first configuration, the single wire assembly is substantially cylindrically shaped. In the second configuration, however, the wires are compressed and are deployed to extend laterally outward from the axis in a bowed configuration.
In the operation of a single wire assembly, the assembly is first inserted into the bone while it is in its first configuration. The actuator is then manipulated to change the single wire assembly from its first configuration into its second configuration. This is done to establish a rigid interaction between the deployed wires and the bony structure of the bone into which the assembly has been inserted. It is in this second configuration that the single wire assembly provides the supportive forces for the skeleton.
Depending on how the single wire assembly is to be used, it can either be a primary type assembly, or a secondary type assembly. The essential difference between the two types of assemblies is the structural cooperation between the actuator and the central shaft. For a primary type assembly, the central shaft will have a threaded first end, and it will have a second end that is mounted for rotation on the base member. In this case, the compression plate is formed with a threaded hole to receive the threaded first end of the central shaft. A bolt head that is affixed to the second end of the central shaft can then be manually rotated. This rotation will then change the distance "d" between the base member and the compression plate, to thereby move the primary type assembly from its first configuration into its second configuration.
For the secondary type assembly, the central shaft still has a threaded first end, but the second end is fixedly mounted on the base member. In this case, the compression plate is formed with a hole, and the actuator is a nut that is threaded onto the first end of the central shaft to urge the compression plate toward the base member. Rotation of this nut then moves the compression plate toward the base member to change the distance "d" between the compression plate and the base member. This then moves the secondary type assembly from the first configuration to the second configuration.
As implied above, it is to be appreciated mat various combinations of primary type and secondary type wire assemblies can be made to form the different embodiments of the present invention. One such embodiment is a bipartite wire assembly that includes both a primary type assembly and a secondary type assembly. For the bipartite wire assembly, a primary type assembly and a secondary type assembly are coaxially aligned with each other. Also, they have a common base member.
In a variation of the bipartite wire assembly, the common base member has at least one end that is formed with a step. Specifically, this stepped end will have a first surface that is located at a distance "d1" from the compression plate, and it will have a second surface that is located at a distance "d2" from the compression plate. A first plurality of wires will then interconnect the first surface of the step with the compression plate and a second plurality of wires will interconnect the second surface of the step with the compression plate. In another embodiment of the present invention a compound wire assembly includes a bipartite wire assembly and a primary type assembly. The interaction between these assemblies requires that the base member of the primary assembly be an elongated hollow cylinder that is formed with a longitudinal lumen. Additionally, the base member of this embodiment will be formed with a transverse hole that crosses the lumen at an angle "φ". Specifically, this transverse hole receives the bipartite wire assembly to position the common base member of the bipartite wire assembly across the lumen of the base member. This embodiment also includes a screw that is inserted into the lumen of the base member to urge against the common base member of the bipartite wire assembly. Thus, pressure from the screw holds the bipartite wire assembly on the primary type assembly for establishment of the compound wire assembly.
BRIEF DESCRIPTION OF THE DRAWINGS The novel features of this invention, as well as the invention itself, both as to its structure and its operation, will be best understood from the accompanying drawings, taken in conjunction with the accompanying description, in which similar reference characters refer to similar parts, and in which:
Fig. 1A is an elevation view of a single wire assembly in a configuration before being deployed;
Fig. 1B is a view of the single wire assembly shown in Fig. 1A after being reconfigured into a deployed configuration;
Fig. 2A is an elevation view of a bipartite wire assembly in a configuration before being deployed;
Fig. 2B is a view of the bipartite wire assembly shown in Fig. 2A after being reconfigured into a deployed configuration;
Fig. 3 is a view of a compound wire assembly in a configuration before being deployed; Fig. 4 is a cross section view of a femur, shown with a compound wire assembly of Fig. 3 deployed to replicate biomechanical stresses in the femur head; and
Fig. 5 is a schematic view of Singh lines in a femur. DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring initially to Fig. 1A, a primary type assembly is shown and is designated 10. As shown, the primary type assembly 10 is in a first configuration with a plurality of wires 12 (of which wire 12a is labeled and is exemplary) oriented substantially parallel to one another. It can be seen that the plurality of wires 12 extend between a base member 14 enclosed by an outer sleeve 16 and a compression plate 8 at a distance "d". An additional essential structural component is a central shaft 22 that interconnects the base member 14 and the compression plate 18. In detail, the central shaft 22 has a first end 24 that is received into a threaded opening 26 in the compression plate 18. And, the central shaft 22 is also constructed with a second end 28 that is also threaded and extends into a threaded opening 30 constructed in the center of the base member 14. At its second end 28, the central shaft 22 is formed with an actuator 32 that will be used to manipulate the primary type assembly 10 between the first configuration and the second configuration.
When viewed in conjunction with Fig. 1A, Fig. 1B can be used to describe the movement of the primary type assembly 10 from its first configuration (Fig. 1A) to its second configuration (Fig. 1B). The initial step is to insert the assembly 10 into a bone, while the primary type assembly 10 is in Its first configuration. Once the primary type assembly 10 has reached a predetermined location in the bone, the actuator 32 is engaged to urge the base member 14 towards the compression plate 18. When the actuator 32 is engaged, the base member 14 moves a distance "Δd". During the movement of the base member 14 towards the compression plate 18, the plurality of wires 12 bow outward as shown in Fig. 1B. The wires 12 continue to bow outward until contact is established between the solid, bony surface of the inside of the bone into which the primary type assembly 10 has been inserted. In contacting the bony surface, the primary type assembly 10 is positioned securely against the bone and is able to closely replicate the supportive forces present if the bone was healthy.
Now referring to Fig. 2A, a bipartite assembly 36 is shown in a first configuration. It can be seen that the bipartite assembly 36 is constructed with two coaxial assemblies 10a, b connected by a common base member 38. Assembly 10a is a primary type assembly, as depicted in Fig. A and 1B, having a central shaft 22a, first end 24a, a threaded opening 26a, and an actuator 32 as described above. In this case, assembly 10b is a secondary type assembly that differs slightly from assembly 10a. Like the primary type assembly 10a, assembly 10b is formed with a central shaft 22b with a threaded first end 24b that passes through a threaded opening 26b in the compression plate 18b. Unlike the primary type assembly 10a, a nut 40 is formed on the central shaft 22b to serve as the mechanism for moving the secondary type assembly 10b between the first and second configuration. In other words, the nut 40 replaces the actuator 32 that is used with a primary assembly 10. As shown, the distance between compression plate 18b and the common base member 38 is "d1." And, the distance between compression plate 18a and the common base member 38 is "d2."
Referring to Fig. 2B, a bipartite wire assembly 36 is shown in its second configuration. Here, the actuator 32 of assembly 10a and the nut 40 of assembly 10b have both been engaged. As such, each assembly 10a, b moves from the first configuration to the second configuration. In detail, the actuator 32 moves the compression plate 18a of assembly 10a towards the common base member 38. Also, upon engagement of the nut 40, compression plate 18b of assembly 10b is moved towards the common base member 38. It can be seen that the wires (of which 12a, 12b are exemplary) on both assembly 10a and assembly 10b are both bowed outward in the second configuration of the bipartite wire assembly 36. As shown, the distance that compression plate 18a moves is Δd1, and the distance compression plate 18b moves is Δd2. The values for Δd1 and Δd2 do not have to be equal and will be based on the structure of the individual bone into which the bipartite wire assembly 36 has been inserted.
In Fig. 3, a compound wire assembly 42 is shown in a first configuration before being deployed into a bone. As shown, the compound wire assembly 42 is formed by inserting a bipartite wire assembly 36 into a transverse hole 44 formed on an elongated base member 46 of a primary type assembly 10. This transverse hole 44 crosses the elongated base member 46 at an angle "Φ," which is determined by the orientation required for the use of the bipartite assembly 36 after insertion into a particular bone. An additional feature of the elongated base member 46 used with the compound wire assembly 42 is a stabilizing screw 48. When tightened, the stabilizing screw 48 contacts the outer surface of the common base member 38 to stabilize the joining of the primary type assembly 10 and the bipartite wire assembly 36. In all other aspects, the individual assemblies that make up the compound wire assembly 42 are substantially the same as disclosed previously.
Referring now to Fig. 4, a compound wire assembly 42 is shown in an operational environment in a femur 50. It can be seen that the compound wire assembly 42 is in its second configuration with the wires of the primary type assembly 10 and the bipartite wire assembly 36 bulging outward to make contact with the interior surface of the bone.
Finally, referring to Fig. 5, Singh lines in a femur 50 are shown. Stated simply, Singh lines are radiologically evaluated stress lines in a bone. These lines indicate the tensile forces 52 and compressive forces 54a, 54b, 54c a bone must withstand. Consequently, these tensile forces 52 and compressive forces 54a-c are the same forces the device of the present invention will counteract when inserted into a bone. Prior to the selection of a specific assembly, the Singh lines of a bone will be modeled and analyzed. Once the Singh lines have been modeled and analyzed, a particular assembly (primary, secondary, bipartite, compound) can be selected and customized to replicate the tensile forces 52 and compressive forces 54a-c indicated by the Singh lines.
While the particular Device for Establishing Supportive Forces in the Bony Structure of a Skeleton as herein shown and disclosed in detail is fully capable of obtaining the objects and providing the advantages herein before stated, it is to be understood that it is merely illustrative of the presently preferred embodiments of the invention and that no limitations are intended to the details of construction or design herein shown other than as described in the appended claims.
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|Cooperative Classification||A61B17/7275, A61B17/744, A61B17/7233|
|5 Dec 2012||121||Ep: the epo has been informed by wipo that ep was designated in this application|
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